|Publication number||US6659936 B1|
|Application number||US 10/049,071|
|Publication date||Dec 9, 2003|
|Filing date||Aug 4, 2000|
|Priority date||Aug 4, 1999|
|Also published as||CA2378388A1, CA2378388C, DE60036873D1, DE60036873T2, EP1207822A1, EP1207822A4, EP1207822B1, US7384390, US20040116773, US20050119710, US20080195172, WO2001010357A1|
|Publication number||049071, 10049071, PCT/2000/925, PCT/AU/0/000925, PCT/AU/0/00925, PCT/AU/2000/000925, PCT/AU/2000/00925, PCT/AU0/000925, PCT/AU0/00925, PCT/AU0000925, PCT/AU000925, PCT/AU2000/000925, PCT/AU2000/00925, PCT/AU2000000925, PCT/AU200000925, US 6659936 B1, US 6659936B1, US-B1-6659936, US6659936 B1, US6659936B1|
|Inventors||John B Furness, Robert W Barnett, Helen E O'Connell, George D Hirst|
|Original Assignee||University Of Melbourne|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (41), Non-Patent Citations (1), Referenced by (68), Classifications (14), Legal Events (7)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This invention relates to prosthetic devices for the treatment of urinary incontinence and, in particular, to prosthetic devices employing transplanted tissue.
The present invention is concerned with forms of incontinence caused wholly or partly by inadequate sphincter function. This may include forms of stress incontinence, urge incontinence and total incontinence. The invention has been developed initially for use in treating male incontinence and will be described principally with respect to that application. However, it will be appreciated by those skilled in the art that the invention is also applicable for use in treating female incontinence.
Incontinence is a major health problem, particularly with the ageing population, for which there is no well-accepted medical treatment. For females, surgically constructed slings are increasingly being used for stress incontinence and with increasing success. However, here is no low risk and reliably effective treatment for moderate to severe male stress incontinence particularly after treatment of prostate cancer. As the incidence of prostate cancer is increasing, this is a growing health issue.
The internal sphincter of the urethra consists of smooth muscle cells interposed with elastic tissue and is located in the proximal urethra. Its constant tone is crucial to maintaining mechanical resistance in the proximal urethra sufficient to hold back the passive pressure exerted by urine in the bladder. Weakness in this area is a common cause of urinary incontinence, for example after treatment for prostate cancer.
Prosthetic sphincter valves have been proposed in numerous forms, including mechanical, hydraulic and electrical devices which replace or supplement the defective damaged internal sphincter of the urethra (e.g. PT 101841, SE 931516, GB 2266844, FR 2638964, WO97/01309 and U.S. Pat. No. 4,619,245). Electrical stimulation of the muscles of the sphincter has also been proposed (DE 29614895). Other approaches have proposed the use of external or implanted electrodes to stimulate existing sphincter function.
A variety of approaches have been proposed in relation to the electrical stimulation of the muscles of the sphincter, most of which are directed towards stimulating an existing sphincter and/or muscles disposed about, for example, a bladder(DE 29614895).
Another group of prior art proposals for the treatment of incontinence are directed towards the stimulation of sacral nerves and the like. Such proposals again seek to use the existing muscle structures. (U.S. Pat. No. 4,771,779, U.S. Pat. No. 4,703,775, U.S. Pat. No. 4,607,639, U.S. Pat. No. 3,870,051, U.S. Pat. No. 4,688,575, U.S. Pat. No. 4,389,719 and U.S. Pat. No. 5,702,428).
Other stimulation means have been proposed, for example U.S. Pat. No. 5,562,717, wherein stimulating electrodes are disposed on the skin of a person to externally stimulate existing muscles to control incontinence. This method is disadvantageous in that it requires electrodes to be disposed in a predetermined location of the person and be electrically connected to a power source therefore not allowing complete freedom.
It has also been proposed to implant part of a small skeletal muscle from the thigh around the patient's urethra, and then to electrically stimulate the muscle to “retrain” it to function as a replacement sphincter (New Scientist, Jun. 29 1996). However, this approach, even if successful, would require relatively high levels of electrical stimulation to allow sufficient contracture of the replacement sphincter.
It is an object of the present invention to provide an improved prosthetic device for use in treating incontinence.
Broadly, the present invention utilises innervated smooth muscle to provide an auxiliary sphincter. This is stimulated by a suitable device in order to provide a functional sphincter in the patient. As a consequence, the stimulator device can operate with lower power consumption, and produce a superior sphincter action.
According to a first aspect of the invention there is provided an implantable sphincter stimulator configured for operatively providing electrical stimulation to a surgically implanted innervated smooth muscle sphincter disposed about a urethra so as to control the flow of urine therethrough, the stimulator including:
a stimulus generating unit in electrical communication with a receiver, the stimulus generating unit operatively configured to provide a first predetermined electrical stimulation signal adapted to contract said sphincter, and a second predetermined signal adapted to allow said sphincter to relax, one of said predetermined signals being selected in response to a signal received at the receiver from a remote controller.
In preferred embodiments, the stimulator applies the first stimulation signal, unless a signal is received indicating that the patient wishes to empty the bladder. The second stimulation signal may be simply the absence of a stimulation, a lower level signal or an alternative signal.
Preferably, the stimulation signal is one which will maintain a continuous tone in the innervated sphincter. In other preferred embodiments of the invention the stimulation signal is pulsatile. Preferably, the stimulator provides multiple channel pulse generation. Preferably also, the stimulation pulse frequency is in the range of 0.25 to 2.5 Hz and having a width in the range of 0.05 to 0.20 milliseconds.
Preferably the stimuli applied have a current less than or equal to 30 mA. More preferably, the stimulation signal is generally rectangular and symmetrical biphasic, although alternative biphasic pulses may be used.
Preferably, the sphincter stimulator includes a replaceable or rechargeable battery power source, preferably one which is in-situ rechargeable, for example inductively.
Preferably, the signal to the receiver is communicated by microwave or radio means, optically or by magnetic energy and the receiver respectively is a microwave, radio, photon or magnetic energy receiver.
Preferably, the stimulus generating unit includes a demodulator responsive to the received signal for providing a modulated signal to a stimulus encoder which in turn provides a signal to a stimulus driver. The stimulator preferably includes two or more electrodes for operatively delivering the stimuli to the sphincter. The stimuli may differ between electrodes, or may be the same at each.
Preferably, after the sphincter has been relaxed, the stimulator is adapted to supply the first stimulation signal to contract the sphincter when a predetermined signal to contract the sphincter is not received by the receiver after a predetermined period.
Preferably, the sphincter stimulator includes a transmitter for transmitting sphincter stimulator telemetry information indicative of one or more parameters of the stimulator for detection remotely. Preferably, the information is transmitted by means of radio waves, microwaves, optically or by magnetic energy. More preferably, the parameters include one or more of the stimulation signal frequency, current, width and/or shape, and/or of the received signal strength and battery status. Preferably, the stimulus generating unit includes a processing device with non-volatile memory.
Preferably, the receiver is configured to accept a remotely generated sphincter stimulator calibration signal and in response, the stimulus generation unit selectively varies one or more of the stimulation signals. More preferably, the calibration signal is transmitted in response to received sphincter stimulator telemetry information, for example the telemetry signals from the stimulator.
Preferably, the stimulator is in electrical communication with the sphincter by at least one electrical lead having two or more electrodes which are operatively implanted into the sphincter at a predetermined location. More preferably, the lead includes three electrodes disposed in an epimysal, cuff or tripolar configuration about the sphincter.
Preferably, the smooth muscle is taken from the smooth muscle of the bladder and transplanted about the urethra and having its circulation intact. Alternatively, the muscle is venous smooth, anococcygeus smooth muscle, terminal ileum transplanted as a segment devoid of mucosa and having its circulation intact. A further alternative is the dartos smooth muscle from the scrotum or labia. In each case, the long axes of the muscle cells are disposed substantially circumferentially about the sphincter. Depending upon the muscle selected, the circulation may or may not be transplanted intact. If the circulation is not transplanted intact, new vessels will need to be regrown, or otherwise provided.
According to a second aspect of the invention there is provided a system for use in treating bladder incontinence in a person, the system including:
a portion of innervated smooth muscle tissue configured to define a sphincter and implanted substantially circumferentially about the urethra of the person;
an implanted sphincter stimulator arranged so as to allow electrical stimuli to be applied to the sphincter; and
a non-implanted controller in communication with the sphincter stimulator for selectively triggering the generation of predetermined electrical stimulation signals to respectively contract the sphincter or allow the sphincter to relax.
Preferably, the smooth muscle is in the form of a strip and is generally rectangular. More preferably, the strip has dimensions in the range from 4.5 cm to 7.5 cm by 1.25 cm to 2.25 cm. Also preferable, the muscle is disposed substantially fully around the urethra in a generally cylindrical arrangement such that the long axes of the muscle cells are substantially circumferentially aligned.
Preferably, the smooth muscle is selected from those described above.
Preferably, the system includes a sphincter as described above.
Preferably, the controller includes:
means for generating a predetermined signal at the transmitter;
a power source; and
actuation means for selectively generating a signal such that on receipt of the signal, the sphincter stimulator provides the stimulation signal at its output for contracting the sphincter or allowing it to relax. The signals for selecting relaxation or contracture may be different, or the same signal may trigger alternation of states.
One form of the controller, particularly for use by a physician, may include a receiver for receiving the sphincter stimulator telemetry information signal from the sphincter stimulator. Preferably, the signal is transmitted by radio waves, microwaves, optically or by magnetic energy and receiver respectively is a radio, microwave, photon or magnetic energy receiver.
Preferably, the system includes a remote sphincter stimulator programming unit for selectively programming the sphincter stimulator to provide a predetermined output. Preferably, one or more of the stimulation signal current, shape, frequency and width is variable in response to the calibration signal provided by the programming unit. More preferably, the programming unit includes a transceiver for providing the programming signal to the stimulator. The programming unit may conveniently be the physician controller.
According to a third aspect of the invention there is provided a method of using an implantable sphincter stimulator for treating bladder incontinence, the method including the steps of disposing an innervated smooth muscle sphincter about a urethra, arranging one or more electrodes so as to allow stimulation of the neural structures of said sphincter, said electrodes being connected to the sphincter stimulator, so that post implantation, a predetermined stimulation signal may be applied by a stimulus generating unit to selectively contract the sphincter or allow it to relax.
Preferably, the method includes the step of transmitting the signal to the sphincter stimulator by radio signals, microwaves, optically or by magnetic energy.
Preferably, three electrodes are arranged in the sphincter in an epimysal, cuff or tripolar configuration.
Preferably, the sphincter is smooth muscle selected from those previously described.
According to a fourth aspect of the invention there is provided a method of treating incontinence including the steps of:
disposing an innervated smooth muscle sphincter around a urethra;
locating a plurality of electrodes in predetermined locations in the sphincter and electrically connecting the electrodes with an implanted sphincter stimulator; and
selectively actuating the sphincter stimulator to provide a predetermined stimulation signal to either contract the sphincter or allow it to relax in response to a remotely generated signal.
According to another aspect of the invention there is provided a method of surgically implanting a sphincter stimulator in a system for treating urinary incontinence, including the steps of:
implanting the innervated smooth muscle sphincter about the urethra in a person;
implanting the electrodes into the sphincter at predetermined locations; and
implanting the sphincter stimulator, the arrangement being such that the electrodes are electrically connected to the sphincter controller to permit stimulation signals from said sphincter stimulator to stimulate the neural structures of said smooth muscle.
Implanting in this context includes transplanting from the same or another person, or the use of externally prepared smooth muscle tissue. In each aspect, it is preferred that the implanted sphincter function so as to substantially prevent leakage of urine when contracted. In general, the main function of the innervated muscle prosthesis is to augment function in the internal sphincter. It should not be used to override any natural sphincter function that may be preserved. The sphincteric pressure exerted by the prosthesis should be sufficient to restore the net sphincteric resistance to its normal level of operation. Unnecessarily high pressure would not only be wasteful of internal stimulator energy but could also cause dangerous overfilling of the bladder. On the other hand, the pressure must be sufficiently high to prevent the leakage of urine.
The smooth muscle tissue may be selected from those described above, or any other suitable smooth muscle tissue. It will be appreciated by those skilled in the art that other types of smooth muscle may potentially be employed as the implantable sphincter including alpha-adrenergic excitatory innervation, cholinergenic excitatory or, inter alia, circular intestinal muscle.
One advantage of using smooth muscle tissue is that it physiologically performs a sphincteric-like function and the muscle layer should be able to be transplanted whilst maintaining its innervation, or allowing for its reinnervation, and blood supply. Moreover, smooth muscle of the types described is readily reinnervated by sympathetic nerves should the existing innervation be damaged during surgery. Reinnervation may take some time, for example, two to three weeks, after surgery.
Another advantages associated with the use of an innervated smooth muscle sphincter in accordance with the present invention is that in smooth muscle, a long-lasting contracture (2-3 seconds) results from a single neural stimulation. Accordingly, only a low frequency of stimulation is required to produce a tetanic contraction especially where it is moderated by neurotransmitter release.
The tension generated per unit cross-sectional area of smooth muscle is greater than for skeletal muscle. Smooth muscle generates tension over a wide length/tension relationship, that is, it continues to generate tension even when partially contracted. Smooth muscle is able to maintain high tension with relatively low energy expenditure. Smooth muscle tissue generally displays a persistent generation of tone during low frequency repetitive nerve stimulation.
A further advantage of the use of smooth muscle according to the present invention is that low frequency nerve stimulation causes the release of a chemical transmitter. Stimulating the nerves within smooth muscle invariably triggers a contraction because the neurotransmitter interacts with a receptor. The activated transmitter/receptor complex then activates a second messenger pathway and releases calcium ions from internal stores. It is relevant that calcium is the final trigger in the contraction of both skeletal, smooth or cardiac muscle. When stores release calcium they do so for extended periods of time, typically in the order of several seconds. Therefore, if the exciting pathway is triggered repeatedly at low frequencies a sustained rise in calcium occurs and the smooth muscle develops a contracture. That is, it does not relax between stimuli. In some smooth muscles, a few stimuli delivered every two seconds, for example, will lead to a sustained contraction.
An alternative way to excite smooth muscle is to stimulate it directly which produces quite long lasting contractions but only on application of very high stimulating voltages. Nerves have low thresholds for activation, compared with muscles, and this, together with the low frequencies of activation required, means that stimulus spread will be avoided. Importantly, an electrical device can reasonably be expected to survive untouched for many years with such low usage demands.
A preferred embodiment of the invention will now be described, by way of example only, with reference to the accompanying drawings in which:
FIG. 1 is a schematic illustration of a system for treating incontinence according to the invention;
FIG. 2 schematically illustrates the implanted sphincter stimulator of FIG. 1;
FIG. 3 schematically illustrates external and implanted parts of the system of FIG. 1;
FIG. 4 illustrates a sphincter stimulator programming unit and sphincter stimulator of the system of FIG. 1;
FIG. 5 is an alternative schematic illustration of the system of FIG. 1 showing a preferred configuration of electrodes; and
FIG. 6 is an enlarged view of the electrode configuration of FIG. 5.
Referring in general to FIGS. 1 to 6, there is illustrated an implantable sphincter stimulator 1 for selectively providing electrical stimulation to an innervated smooth muscle sphincter 2 disposed about a urethra 3 for controlling the flow of urine.
Stimulator 1 includes a signal processing unit 4 in electrical communication with a receiver 5. Signal processing unit 4 is configured to provide a predetermined electrical stimulation signal at a first output 6 of stimulator 1 in response to a signal generated remotely by controller 7 and applied at receiver 5 such that processing unit 4 selectively provides the stimulation signal to either contract sphincter 2 to substantially block the flow of urine along the urethra 3 or to allow sphincter 2 to relax and allow urine to flow.
Referring to FIG. 2 particularly, signal processing unit 4 includes a demodulator 8 responsive to the signal received at receiver 5 for providing a modulated signal to a stimulus encoder 9 which in turn provides a signal to a stimulus driver 10 which provides the stimulated signal at sphincter stimulator output 6.
Once sphincter 2 is allowed to relax, processing unit 4 includes means to supply a stimulation signal at output 6 to contract sphincter 2 when a predetermined signal to contract the sphincter is not received by signal processing unit 4 via receiver 5 for a predetermined time period. In the preferred implementation, the processing unit 4 provides stimuli adapted to contract the sphincter unless a signal is received, in response to which the stimuli is turned off, and the sphincter relaxes.
The signal is communicated to sphincter stimulator 1 by means of radio frequency waves and receiver 5 is an RF receiver. If the casing of the stimulator is made of titanium, and the receiver is inside, then a frequency of 8-10 kHz is preferred. If the casing is made of silicone rubber or the like, then 8-10 MHz is preferred.
In other embodiments of the invention, the signal may be communicated optically in the range 630 nm to 1400 nm to sphincter stimulator 1 and receiver 5 is a photon detector in the form of a PMT, photo-diode or other suitable detector.
In yet other embodiments of the invention, the signal is communicated to sphincter stimulator 1 by microwave means and receiver 5 is a microwave receiver. In such embodiments, the microwave signal has a frequency in the range of 0.9 to 2.5 GHz. Alternatively, the signal is communicated to sphincter stimulator 1 by magnetic means and receiver 5 is a magnetic energy receiver. Any other suitable communication arrangement may be used.
As is best illustrated in FIG. 3, controller 7 includes the RF transmitter which is driven by a means for generating the control signal. Controller 7 further includes actuation means for selectively generating the control signal at transmitter 11.
Part of transmitter 11 is also a receiver for receiving an information signal indicative of at least one parameter of the sphincter stimulator and provided by the sphincter stimulator. The telemetry information signal is transmitted to the controller by means of a transmitter disposed within receiver 5. In embodiments of the invention where microwaves are employed to communicate either the control signal or telemetry information signal, transceiver 11 of controller 7 is configured to transmit and receive microwave radiation. In embodiments where the control signal is transmitted optically, transceiver 11 includes a photon detector in the form of a PMT or solid state device and a light source having a predetermined output. In embodiments of the invention where the control signal and the sphincter stimulator information signal are transmitted by magnetic energy, the transmitter receiver 5 functions as a passive proximity card and controller 7 functions as the active proximity card reader.
FIG. 2 illustrates a stimulation signal in the form of a pulse. The pulse is generally rectangular and symmetrically biphasic. In other embodiments of the invention, not illustrated, sphincter stimulator 1 provides multiple channel pulse generation at output 6. The stimulation signal is selected so as to provide a substantially continuous tone in the sphincter.
The stimulation signal provided at output 6 has a substantially constant current less that or equal to 30 mA, and preferably of the order of 15 mA. The stimulation pulse frequency provided to sphincter 1 by output 6 is in the range of 0.25 Hz to 2.5 Hz and is preferably 2 Hz. The stimulation pulse width is in the range of 0.05 ms to 0.2 ms and is preferably 0.15 ms. It should be noted that the device is current regulated, and accordingly the stimulation voltage will vary with the resistance of the muscle tissue between the electrodes. Typical values for the voltage are between 0.2 and 7 volts.
It should be noted, however, that these parameters are variable and are configured for each person.
Preferably, the smooth muscle is taken from the smooth muscle of the bladder and transplanted about the urethra and having its circulation intact.
Alternatively, the muscle may be venous smooth, anococcygeus smooth muscle, terminal ileum transplanted as a segment devoid of mucosa and having its circulation intact. A further alternative is the dartos smooth muscle from the scrotum or labia. Any other suitable muscle may be employed. In each case, the long axes of the muscle cells are disposed substantially circumferentially about the sphincter.
The muscle is generally in the form of a rectangular strip such that the long axes of the muscle cells are disposed substantially lengthwise along the strip. The muscle is then disposed substantially fully around the urethra in a generally cylindrical arrangement such that the long axes of the muscle cells are substantially circumferencially disposed about the urethra. Preferably, the strip is completely disposed around the urethra.
The muscle strip has dimensions 6 cm by 2 cm and is preferably provided in the range from 4.5 cm to 7.5 cm by 1.25 cm to 2.25 cm.
The stimulation signal is provided at output 6 of sphincter stimulator 1 is supplied to sphincter 2 by an electrode implanted into the sphincter at a predetermined location and an electrical lead 16 being disposed intermediate. As is best illustrated in FIG. 6, lead 16 includes three electrodes disposed in a tripolar configuration about sphincter 2 and having means to electrically connect to lead 16. In other embodiments of the invention, the three electrodes are disposed in a cuff or epimysal configuration about the sphincter.
Electrode leads may extend between the pulse generator and the electrodes, allowing some “slackness” in their length to account for normal body to movements.
As is best illustrated in FIGS. 5 and 6, the configuration of the electrodes are disposed in a tripolar configuration. Simple tripolar electrodes are the least expensive alternative, are relatively easy to implant and can be used to stimulate the transplanted smooth muscle. Their exposed metallic surfaces usually consist of a cathode aligned between two anodes.
In the epimysial configuration, the electrodes are sutured directly onto the surface of a muscle. These electrodes are implemented when stimulation of a motor nerve trunk is impractical, however, this is not necessarily always the case.
In the cuff electrode configurations are employed in alternative embodiments and are contained within an insulating sheath substantially circumferentially around the circumference of the transplanted sphincter. They are capable of stimulating the embedded nerve fibres maximally while keeping the stimulus field local to the transplant.
In other embodiments of the invention, not illustrated, the sphincter stimulator includes a second output such that one of the sphincter stimulator outputs provides a signal to contract the sphincter and the other output provides a stimulation signal to allow the sphincter to relax or contract to a lesser extent. In this embodiment, each of the first and second outputs of the sphincter stimulator each include a lead having three outputs in a tripolar configuration about the sphincter. In yet other embodiments, the first and second outputs each include a lead having three electrodes disposed in a cuff or epimysal configuration about the sphincter.
It will be appreciated that in normal use, only two of the three electrodes will be used to deliver stimuli. The third electrode is provided as a spare, in the event that one of the electrodes ceases to function. However, it is contemplated that the present invention could use a more complicated set of stimuli, or more electrodes.
Sphincter stimulator 1 includes a replaceable battery power source 17, not illustrated in FIG. 2. In one implementation, battery 17 is in electrical communication with signal processing unit 4 such that the control signal provided by controller 7 to sphincter stimulator 1 inductively provides energy to recharge the battery. In another implementation, in the case of radio frequency transceiving between the and sphincter stimulators, the signal is provided by modulating the RF signal such that the signal processing unit extracts the control signal and provides the battery with remaining power from the RF signal.
As is best illustrated in FIG. 4, RF transceiver 5 of stimulator 1 is communicable with a third output of processing unit 4 for transmitting sphincter stimulator telemetry information indicative of one or more the parameters of the sphincter stimulator for remote detection. The information is transmitted by radio frequency signals, however, in other embodiments of the invention the sphincter stimulator information is transmitted by microwave means, optical means or by magnetic energy. The sphincter stimulator information signal includes information regarding parameters such as stimulation signal-frequency, current, width and/or shape, and received signal strength and battery status. This is useful for use in a controller intended for use by physicians.
A remote sphincter stimulator programming unit 13 is adapted to receive the sphincter stimulator information provided by receiver 5. The sphincter stimulator programming unit includes a transceiver 14 for providing a calibration signal to stimulator 1 which, in response, selectively varies one or more of the output properties of stimulator 1. The calibration signal is preferably transmitted in response to receiving the sphincter stimulator telemetry information. The calibration signal includes coding to selectively vary the output current, shape, frequency and/or width. Conveniently, the remote sphincter stimulator programming unit is integrated into the physician controller.
The preferred embodiments of the invention also provide a method of treating urinary incontinence in a person including the steps of disposing the implanted smooth muscle sphincter substantially around a urethra, locating a plurality of electrodes in predetermined locations in the sphincter and electrically connecting them with an implanted sphincter stimulator as hereinbefore described.
The sphincter stimulator is then selectively actuated on receipt of the control signal to provide the predetermined stimulation signal to either contract the sphincter or allow it to relax. The method includes providing the stimulation signal to contract the urethra or allow it to relax from output 6 of sphincter stimulator 1. In other embodiments of the invention, however, the stimulation signal to contract the sphincter about the urethra is provided by a separate output of sphincter stimulator 1 to that which provides a stimulation signal to allow the urethra to relax.
There is also provided a method of surgically implanting a sphincter stimulator system as hereinbefore described in a person for treating incontinence, the method including the steps of implanting the smooth muscle sphincter substantially about the urethra in a person, implanting the sphincter stimulator in the person proximal to the implanted sphincter and implanting electrodes into the sphincter at predetermined locations and electrically connecting the sphincter stimulator with the smooth muscle sphincter.
Other preferred embodiments provide a stimulus system including circuit means defining a single channel electrical pulse generator, power supply means, a control circuit to allow a transplanted sphincter to relax, a separate control circuit to adjust pulse parameters, two or more stimulus electrodes, and leads connecting the stimulator to the electrodes.
The prosthetic sphincter includes a sheath of innervated or reinnervatable muscle tissue taken from the selected muscle and transplanted around the urethra. In one embodiment, a segment of distal small intestine, 2-3 cm long, on a vascular pedicle is isolated and the remaining intestine is rejoined by end to end anastomosis. The isolated segment is opened along its antimesenteric border and the mucosa is dissected away.
The isolated segment is drawn down to the neck of the bladder. It is then taken around the bladder neck, so that the circular muscle is disposed substantially circumferentially with respect to the neck, and the cut antimesenteric borders are sewn together to create a close fit around the neck of the bladder. If necessary, the circumferential length is reduced to create a close fit. The newly created and vascularised sphincter is secured in place by sewing it to the superficial connective tissue of the bladder neck. A stimulating electrode assembly is sewn to the transplanted intestine, with the axis of the electrode assembly at right angles to the circular muscle, adjacent to the entry of the vessels from the vascular pedicle. The anchoring ligatures penetrate the sphincter and are secured to the underlying bladder neck.
In an alternative embodiment, the sphincter augmentation is made by dissecting the anococcygeus muscles from their spinal insertions, and drawing the freed muscle around the bladder neck. The sphincter may also be created from a section of muscular vein, venous smooth muscle, the terminal ilium and transplanted as a segment devoid of mucosa and having its circulation intact, or the dartos smooth muscle from the scrotum or labia.
The stimulus pulse generator transfers electrical pulses to the electrodes and these pulses are converted into action potentials in the nerves transplanted with the muscle sphincter or in the nerves which re-innervate the sphincter after surgery.
All implanted circuitry is preferably sealed and encased in a biologically inert material such as a biocompatible silicone material. The metallic electrodes and leads are preferably of Platinum-Iridium alloy. The connecting wires are preferably insulated with a silicone coating and lead to an implanted control unit placed between the abdominal muscle and skin.
The stimulator is required to maintain continuous tone in the transplanted sphincter sufficient to hold urine in the bladder without leakage by continuous stimulation. To release urine, an external control unit using, for example, a radio frequency signal will turn off the internal unit to halt the stimulation of the sphincter, and is shown schematically in FIG. 3.
Alterative embodiments of the invention employ microwave or optical means, for example, in the form of infra-red radiation, to communicate the control signal to the sphincter stimulator, and the sphincter stimulator includes a corresponding receiver at or near the skin of the person.
The person would hold the external device adjacent the skin over the implant (and push an actuation button) to allow the transplanted sphincter to relax and urine to flow. After bladder emptying, the patient would then push the button again to resume sphincteric pressure. As described, if the user forgets to push the button to close the sphincter, the stimulator could be programmed to resume operation automatically after a given time.
The advantages of this system are twofold. Firstly, the patient does not need to hold the external control unit against their skin for the whole period of bladder emptying. They simply initiate the process and can then put the unit aside if desired. The second advantage is that such a system allows the stimulator circuitry to be adjusted externally.
In embodiments where the signal is communicated magnetically, a permanent magnet is placed on the surface of the skin directly over the location of the implanted control circuit. The circuit is designed to detect the presence of the magnetic field and shut off the stimulation accordingly. To empty the bladder, therefore, the person simply places a magnet over the implant for the time period required to empty the bladder. A small permanent magnet is a convenient item to carry around and requires no batteries. One disadvantage of such a system is that a magnetic detector needs to be added to the implanted device and this, in turn, requires more power from the internal batteries.
It is envisaged that the requirements of the stimulator may change, both post-operatively and with alteration of the preserved sphincteric resistance as the person ages. Access to the implanted device via surgery for the purpose of hardware adjustment is, of course, undesirable. Therefore, adjustment of the stimulus parameters via an external radio link to the sphincter stimulator programming unit 13 is a preferred feature of the system.
It will be appreciated that various modifications and alterations may be made to the system described above without departing from the scope and spirit of the invention.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3870051||Apr 26, 1973||Mar 11, 1975||Nat Res Dev||Urinary control|
|US4106511||Apr 12, 1977||Aug 15, 1978||Svenska Utvecklingsaktiebolaget||Electrical stimulator in remedy of incontinence|
|US4153059||Oct 25, 1977||May 8, 1979||Minnesota Mining And Manufacturing Company||Urinary incontinence stimulator system|
|US4256093||Oct 12, 1978||Mar 17, 1981||The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration||Prosthetic urinary sphincter|
|US4387719||Oct 23, 1981||Jun 14, 1983||Gorenje Tovarna Gospodinjske Opreme N.Sol.O. Velenje||Control circuit of a therapeutic stimulator for the urinary incontinence|
|US4580578||May 3, 1984||Apr 8, 1986||Richard Wolf Gmbh||Device for the treatment of female urinary incontinence|
|US4607639||May 18, 1984||Aug 26, 1986||Regents Of The University Of California||Method and system for controlling bladder evacuation|
|US4688575||Mar 12, 1982||Aug 25, 1987||Duvall Wilbur E||Muscle contraction stimulation|
|US4709690||Apr 21, 1986||Dec 1, 1987||Habley Medical Technology Corporation||Implantable blood flow and occlusion pressure sensing sphincteric system|
|US4711231||Nov 3, 1986||Dec 8, 1987||Aaron N. Finegold||Implantable prosthesis system|
|US4878889||Jun 24, 1988||Nov 7, 1989||American Medical Systems, Inc.||Artificial sphincter device|
|US5117840||May 5, 1989||Jun 2, 1992||Biosonics||Anal sphincter training device|
|US5199430 *||Mar 11, 1991||Apr 6, 1993||Case Western Reserve University||Micturitional assist device|
|US5370671||Jan 28, 1993||Dec 6, 1994||Empi, Inc.||Incontinence electrode apparatus|
|US5478305||Feb 3, 1993||Dec 26, 1995||British Technology Group Group Limited||Prosthetic sphincter device|
|US5562717||May 21, 1993||Oct 8, 1996||Axelgaard Manufacturing Company, Ltd.||Electrical stimulation for treatment of incontinence and other neuromuscular disorders|
|US5588960||Dec 1, 1994||Dec 31, 1996||Vidamed, Inc.||Transurethral needle delivery device with cystoscope and method for treatment of urinary incontinence|
|US5617876||Sep 19, 1994||Apr 8, 1997||Les Enterprises Laborie, Inc.||Apparatus for examining the functioning of body structures comprising smooth muscle walls|
|US5620475||Apr 14, 1995||Apr 15, 1997||Siemens Elema Ab||Extracorporeally controllable medical implant and method for operating same|
|US5667615||May 13, 1996||Sep 16, 1997||Empi, Inc.||Method of making an incontinence electrode|
|US5676160||Jan 31, 1995||Oct 14, 1997||Bryant; Benjamin Jay||Surgical method|
|US5704893||Nov 12, 1996||Jan 6, 1998||Dacomed Corportion||Vessel occlusive apparatus and method|
|US5736590||Nov 7, 1995||Apr 7, 1998||Rasmussen; Lenore||Process for producing an electrically driven mechanochemical actuator|
|US5755758||Nov 7, 1995||May 26, 1998||Medtronic, Inc.||Intramuscular stimulation lead with enhanced infection resistance|
|US5759471||Feb 13, 1997||Jun 2, 1998||Empi, Inc.||Method of making an incontinence electrode|
|US5833595||Sep 6, 1994||Nov 10, 1998||Lin; Vernon Wen-Hau||Treatment of excretory problems|
|US5860940||Jul 23, 1997||Jan 19, 1999||Schoenfeld; Andreas||Method of determining the trainability of a patient suffering from incontinence|
|US6086525||Dec 31, 1997||Jul 11, 2000||Neotonus, Inc.||Magnetic nerve stimulator for exciting peripheral nerves|
|US6243607 *||Sep 4, 1997||Jun 5, 2001||University Technologies International Inc.||Gastro-intestinal electrical pacemaker|
|US6306078 *||Jul 8, 1997||Oct 23, 2001||Vernon Wen-Hau Lin||Treatment of excretory problems|
|US6393323 *||Jan 31, 2000||May 21, 2002||Mcgill University||Electronic stimulator implant for modulating and synchronizing bladder and sphincter function|
|DE4436634A1||Oct 13, 1994||Apr 18, 1996||Kurt Haynl||Anal sphincter muscle training and testing device|
|DE19750043A1||Nov 12, 1997||May 20, 1999||Johann W Prof Dr Bartha||Neuartige Cuff-Elektrode und Verfahren zur Erzeugung dieser|
|EP0348114A1||Jun 16, 1989||Dec 27, 1989||American Medical Systems, Inc.||Artificial sphincter device|
|FR2638964A1||Title not available|
|PT101841A||Title not available|
|SE9301516A||Title not available|
|WO1984001515A1||Oct 10, 1983||Apr 26, 1984||Steindorf Susanne Ruth||Galvanic electrostimulation device for the vesical and anal incontinence and the treatment of hemorrhoids|
|WO1996028211A1||Mar 12, 1996||Sep 19, 1996||Osbon Medical Systems||Therapy apparatus for the functional electromyostimulation of smooth muscle cells|
|WO1997001309A1||Jun 7, 1996||Jan 16, 1997||Fundação E.J. Zerbini||A mechanical sphincter for controlling urinary incontinence and its implantation method|
|WO1998023232A1||Nov 28, 1997||Jun 4, 1998||Claude Cusset||Prosthetic urinary sphincter with external control|
|1||Beard, J., "Muscle Transplant Brings Relief From Incontinence,:" New Scientist Magazine, vol. 150, Issue 2036, Jun. 29, 1996, pg. 20.|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US6862480||Nov 29, 2001||Mar 1, 2005||Biocontrol Medical Ltd.||Pelvic disorder treatment device|
|US6941171 *||Aug 16, 2001||Sep 6, 2005||Advanced Bionics Corporation||Implantable stimulator methods for treatment of incontinence and pain|
|US7368279 *||Nov 23, 2005||May 6, 2008||The Regents Of The University Of Michigan||Three dimensional bioengineered smooth muscle tissue and sphincters and methods therefor|
|US7384390 *||Dec 2, 2004||Jun 10, 2008||The University Of Melbourne||Method and apparatus for treating incontinence|
|US7415308||Apr 28, 2005||Aug 19, 2008||Medtronic, Inc.||Implantable medical device providing adaptive neurostimulation therapy for incontinence|
|US7515965||Apr 28, 2005||Apr 7, 2009||Medtronic, Inc.||Implantable medical device providing adaptive neurostimulation therapy for incontinence|
|US7580752||Apr 28, 2005||Aug 25, 2009||Medtronic, Inc.||Implantable medical device providing adaptive neurostimulation therapy for incontinence|
|US7613516||Nov 28, 2002||Nov 3, 2009||Ams Research Corporation||Pelvic disorder treatment device|
|US7765006||Jul 27, 2010||Leto Medical, Llc||Method and apparatus for providing continence to a gastrointestinal ostomy|
|US7765007||Jul 27, 2010||Leto Medical, Llc||Apparatus and method for providing continence to a gastrointestinal ostomy|
|US7931582||Feb 9, 2001||Apr 26, 2011||Obtech Medical Ag||Controlled impotence treatment|
|US8083663||Jun 17, 2009||Dec 27, 2011||Ams Research Corporation||Pelvic disorder treatment|
|US8096938||Oct 16, 2002||Jan 17, 2012||Obtech Medical Ag||Controlled anal incontinence disease treatment|
|US8096939||Jan 17, 2012||Obtech Medical Ag||Urinary incontinence treatment with wireless energy supply|
|US8126558||May 22, 2006||Feb 28, 2012||Obtech Medical Ag||Controlled penile prosthesis|
|US8160710||Jul 10, 2007||Apr 17, 2012||Ams Research Corporation||Systems and methods for implanting tissue stimulation electrodes in the pelvic region|
|US8190262||Feb 24, 2009||May 29, 2012||Medtronic, Inc.||Adaptive electrical stimulation therapy for fecal incontinence|
|US8195296||May 5, 2006||Jun 5, 2012||Ams Research Corporation||Apparatus for treating stress and urge incontinence|
|US8277426||Sep 30, 2009||Oct 2, 2012||Wilcox Heather J||Male urinary incontinence device|
|US8287444||Apr 29, 2008||Oct 16, 2012||Obtech Medical Ag||Mechanical impotence treatment apparatus|
|US8290594||Aug 19, 2010||Oct 16, 2012||Obtech Medical Ag||Impotence treatment apparatus with energy transforming means|
|US8313423||Nov 20, 2012||Peter Forsell||Hydraulic anal incontinence treatment|
|US8340786||Jun 12, 2008||Dec 25, 2012||Ams Research Corporation||Incontinence treatment device|
|US8372093 *||Oct 27, 2009||Feb 12, 2013||Koletry Processing L.L.C.||Systems and processes for controlling gastric bands based on geographic location|
|US8380312||Dec 30, 2010||Feb 19, 2013||Ams Research Corporation||Multi-zone stimulation implant system and method|
|US8509894||Oct 12, 2009||Aug 13, 2013||Milux Holding Sa||Heart help device, system, and method|
|US8545384||Feb 1, 2010||Oct 1, 2013||Obtech Medical Ag||Anal incontinence disease treatment with controlled wireless energy supply|
|US8556796||Jan 15, 2010||Oct 15, 2013||Obtech Medical Ag||Controlled urinary incontinence treatment|
|US8600510||Oct 9, 2009||Dec 3, 2013||Milux Holding Sa||Apparatus, system and operation method for the treatment of female sexual dysfunction|
|US8602966||Apr 25, 2008||Dec 10, 2013||Obtech Medical, AG||Mechanical impotence treatment apparatus|
|US8636809||Jan 29, 2009||Jan 28, 2014||Milux Holding Sa||Device for treating obesity|
|US8678997||Mar 14, 2006||Mar 25, 2014||Obtech Medical Ag||Male impotence prosthesis apparatus with wireless energy supply|
|US8696543||Oct 14, 2008||Apr 15, 2014||Kirk Promotion Ltd.||Method for controlling flow of intestinal contents in a patient's intestines|
|US8696745||Oct 12, 2009||Apr 15, 2014||Kirk Promotion Ltd.||Heart help device, system, and method|
|US8734318||Jun 28, 2006||May 27, 2014||Obtech Medical Ag||Mechanical anal incontinence|
|US8744585||Apr 28, 2005||Jun 3, 2014||Medtronics, Inc.||Implantable medical device providing adaptive neurostimulation therapy for incontinence|
|US8764627||Sep 10, 2008||Jul 1, 2014||Obtech Medical Ag||Penile prosthesis|
|US8774942||Mar 27, 2012||Jul 8, 2014||Ams Research Corporation||Tissue anchor|
|US8795153||Oct 14, 2008||Aug 5, 2014||Peter Forsell||Method for treating female sexual dysfunction|
|US8874215||Oct 9, 2009||Oct 28, 2014||Peter Forsell||System, an apparatus, and a method for treating a sexual dysfunctional female patient|
|US8961448||Jan 28, 2009||Feb 24, 2015||Peter Forsell||Implantable drainage device|
|US8992409||Apr 12, 2010||Mar 31, 2015||Peter Forsell||Method for controlling flow in a bodily organ|
|US9060771||Jan 29, 2009||Jun 23, 2015||Peter Forsell||Method and instrument for treating obesity|
|US9072907||Oct 12, 2009||Jul 7, 2015||Peter Forsell||Heart help device, system, and method|
|US9192763||Jun 2, 2014||Nov 24, 2015||Medtronic, Inc.||Implantable medical device providing adaptive neurostimulation therapy|
|US9220887||Jun 7, 2012||Dec 29, 2015||Astora Women's Health LLC||Electrode lead including a deployable tissue anchor|
|US20020055761 *||Aug 16, 2001||May 9, 2002||Mann Carla M.||Implantable stimulator systems and methods for treatment of incontinence and pain|
|US20040116773 *||Dec 8, 2003||Jun 17, 2004||Furness John B.||Method and apparatus for treating incontinence|
|US20050049648 *||Oct 12, 2004||Mar 3, 2005||Biocontrol Medical Ltd.||Pelvic disorder treatment device|
|US20050055063 *||Jul 12, 2004||Mar 10, 2005||Loeb Gerald E.||Method and apparatus for the treatment of urinary tract dysfunction|
|US20050119710 *||Dec 2, 2004||Jun 2, 2005||Furness John B.||Method and apparatus for treating incontinence|
|US20050216069 *||Nov 28, 2002||Sep 29, 2005||Biocontrol Medical Ltd.||Pelvic disorder treatment device|
|US20060134076 *||Nov 23, 2005||Jun 22, 2006||The Regents Of The University Of Michigan||Three dimensional bioengineered smooth muscle tissue and sphincters and methods therefor|
|US20060142635 *||Jan 31, 2003||Jun 29, 2006||Peter Forsell||Electrically operable incontinence treatment apparatus|
|US20060149124 *||Jan 31, 2003||Jul 6, 2006||Peter Forsell||Electrically operable impotence treatment apparatus|
|US20060190049 *||Apr 28, 2005||Aug 24, 2006||Medtronic, Inc.||Implantable medical device providing adaptive neurostimulation therapy for incontinence|
|US20060190051 *||Apr 28, 2005||Aug 24, 2006||Medtronic, Inc.||Implantable medical device providing adaptive neurostimulation therapy for incontinence|
|US20060235482 *||May 22, 2006||Oct 19, 2006||Obtech Medicalag||Controlled penile prosthesis|
|US20070100388 *||Oct 31, 2005||May 3, 2007||Medtronic, Inc.||Implantable medical device providing adaptive neurostimulation therapy for incontinence|
|US20070265675 *||May 9, 2007||Nov 15, 2007||Ams Research Corporation||Testing Efficacy of Therapeutic Mechanical or Electrical Nerve or Muscle Stimulation|
|US20080195172 *||Mar 27, 2008||Aug 14, 2008||The University Of Melbourne||Method and apparatus for treating incontinence|
|US20090157139 *||Dec 13, 2007||Jun 18, 2009||Nicholas Martino||Method and apparatus for providing continence to a gastrointestinal ostomy|
|US20090157140 *||Nov 4, 2008||Jun 18, 2009||Nicholas Martino||Apparatus and method for providing continence to a gastrointestinal ostomy|
|US20090163975 *||Feb 24, 2009||Jun 25, 2009||Medtronic, Inc.||Adaptive electrical stimulation therapy for fecal incontinence|
|US20090254145 *||Jun 17, 2009||Oct 8, 2009||Ams Research Corporation||Pelvic disorder treatment|
|US20100010290 *||Sep 4, 2006||Jan 14, 2010||Continence Control Systems International Pty Ltd.||Smooth muscle implant for managing a medical condition|
|US20100016652 *||Sep 25, 2009||Jan 21, 2010||Aram Bonni||Patient-adjustable incontinence device (aid)|
|US20120035496 *||Apr 20, 2010||Feb 9, 2012||Denison Timothy J||Bladder sensing using impedance and posture|
|U.S. Classification||600/30, 607/41|
|International Classification||A61F2/48, A61N1/372, A61N1/36, A61N1/05, A61F2/00, A61F2/08|
|Cooperative Classification||A61N1/05, A61F2/0036, A61N1/36007, A61F2002/0894|
|European Classification||A61F2/00B6B, A61N1/36B|
|Feb 4, 2002||AS||Assignment|
Owner name: UNIVERSITY OF MELBOURNE, THE, AUSTRALIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:FURNESS, JOHN B.;BARNETT, ROBERT W.;O CONNELL, HELEN E.;AND OTHERS;REEL/FRAME:012768/0736
Effective date: 20020124
|Jan 24, 2006||CC||Certificate of correction|
|May 22, 2007||FPAY||Fee payment|
Year of fee payment: 4
|Jun 7, 2011||FPAY||Fee payment|
Year of fee payment: 8
|Jul 17, 2015||REMI||Maintenance fee reminder mailed|
|Dec 9, 2015||LAPS||Lapse for failure to pay maintenance fees|
|Jan 26, 2016||FP||Expired due to failure to pay maintenance fee|
Effective date: 20151209